CN103654823A - Angiographic examination method - Google Patents
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/50—Clinical applications
- A61B6/504—Clinical applications involving diagnosis of blood vessels, e.g. by angiography
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/02—Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computerised tomographs
- A61B6/032—Transmission computed tomography [CT]
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/44—Constructional features of apparatus for radiation diagnosis
- A61B6/4429—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units
- A61B6/4435—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units the source unit and the detector unit being coupled by a rigid structure
- A61B6/4441—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units the source unit and the detector unit being coupled by a rigid structure the rigid structure being a C-arm or U-arm
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/44—Constructional features of apparatus for radiation diagnosis
- A61B6/4429—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units
- A61B6/4458—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units the source unit or the detector unit being attached to robotic arms
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/44—Constructional features of apparatus for radiation diagnosis
- A61B6/4429—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units
- A61B6/4464—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units the source unit or the detector unit being mounted to ceiling
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/48—Diagnostic techniques
- A61B6/486—Diagnostic techniques involving generating temporal series of image data
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/50—Clinical applications
- A61B6/503—Clinical applications involving diagnosis of heart
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
- A61B6/5258—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise
- A61B6/5264—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise due to motion
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
- A61B6/5288—Devices using data or image processing specially adapted for radiation diagnosis involving retrospective matching to a physiological signal
Abstract
A method is provided for angiographic examination of an organ, vascular system or other body regions as the examination object of a patient by means of 4D rotational angiography. A step S1 of the method involves acquisition of projection images (24) in different cardiac phases (c0 to cN). A further step S2 involves reconstruction of 3D volume images (26) in the different cardiac phases (c0 to cN). A further step S3 involves calculation of a motion map (28, 38). A further step S4 includes image combination of the 3D volume images (26) with the motion map (28, 38) to produce resulting, corrected 3D volume images (40) in the different cardiac phases (c0 to cN). A further step S5 involves presentation of the resulting, corrected 3D volume images (40).
Description
Technical field
The present invention relates to a kind of angiography method of organ, vascular system or other body region of patient's conduct inspection object being carried out by 4D rotational angiography.
Background technology
This above mentioned angiography method for example can be by from US7, and angioradiographic system known in 500,784B2 is carried out, and by Fig. 1, it is set forth below.
Standard 4D rotational angiography forms the reconstruction to each volume of each cardiac phase.Typically, these single volumes are subject to the impact of stricture of vagina shape artifact very doughtily, and quantity due to the projection existing in each cardiac phase is little forms for it.
4D rotational angiography, so-called
can carry out with a plurality of rotations, yet only a rotation can be also enough.In standard method, the number of projections existing in each phase place works.Conventionally with rotation
in, each phase place has about 30 projections.In the layer of rebuilding, form stricture of vagina shape artifact thus, as next also will set forth.Use fewer projection, in reconstruction, form more stricture of vagina shape artifacts, because this reconstruction type is not utilized redundancy.
Other carrys out work based on initial data with iterative approximation and Method for minimization from known in the literature method, as being published in Med Phys.2008 February such as Guang-Hong Chen etc., the 35th volume, No. 2, in " the Prior image constrained compressed sensing (PICCS): A method to accurately reconstruct dynamic CT images from highly undersampled projection data sets " of 660-663 page, describe like that.This common very high expense and reconstruction chain (Rekonstruktionskette) that need to be new.
Fig. 1 shows the biplane roentgen system as example, it is for carrying out 4D rotational angiography with the bearing 1 of six-shaft industrial robot or bend arm robot form and fixing C shape arm 2 and the 2' of 1' respectively by two, on the end of C shape arm, be separately installed with roentgen radiation radiation source, for example, with roentgen radiation irradiator 3 and the 3' of Roentgen ray tube and collimator, and be separately installed with roentgen radiation image detector 4 and the 4' as image taking unit.At this, bearing 1 is arranged on floor 5, and the second bearing 1' can be fastened on ceiling 6 places.
By for example from US7,500,784B2 known, preferably there are six pivot centers and there is thus the bend arm robot of six-freedom degree, C shape arm 2 and 2' can be spatially set arbitrarily, for example by by its around it center of rotation between roentgen radiation irradiator 3 and 3' and roentgen radiation image detector 4 and 4' rotate.According to angiography roentgen radiation system 1 to 4 of the present invention, especially can rotate around the turning cylinder in the C shape arm plane of center of rotation and roentgen radiation image detector 4 and 4', preferably can and rotate around the crossing turning cylinder of the mid point with roentgen radiation image detector 4 and 4' around the mid point of roentgen radiation image detector 4 and 4'.
Known bend arm robot has pedestal, and it is for example fixedly mounted on floor 5 or ceiling 6 places.In the mode that can rotate around the first turning cylinder, be fastened with rotating disk thereon.On rotating disk, can robot rocking bar being installed around the rotating mode of the second turning cylinder, on robot rocking bar, in the mode that can rotate around the 3rd turning cylinder, be fastened with robots arm.On robots arm's end, in the mode that can rotate around the 4th turning cylinder, robot is installed.Robot has the tightening member for C shape arm 2 or 2', and it can turn round around the 5th turning cylinder, and can be around the 6th turning cylinder rotation of perpendicular extension.
The implementation of the roentgen radiation diagnostic equipment is not specified industrial robot.Also can use common C shape arm equipment.
Roentgen radiation image detector 4 and 4' can be rectangle or semiconductor detector square, plane, and it is preferably made by unsetting silicon (a-Si).Yet also can use integrated and CMOS detector that may count.
The table top 7 of patient support platform 8 is arranged in the ray path of roentgen radiation irradiator 3 and 3', for taking as the examine patient who checks object.Patient support platform 8 is provided with bench board 9.In the roentgen radiation diagnostic equipment, be connected with the system control unit 10 with picture system 11, this picture system receives and processes the picture signal (for example also not shown executive component) of roentgen radiation image detector 4 and 4'.Then can on the display of monitor suspension system 12, observe roentgen radiation image.Picture system 11 has its function and also will install in greater detail.
Substitute in Fig. 1, illustrate with six-shaft industrial robot or the bearing 1 of bend arm robot form and the roentgen radiation system of 1', can be as at US7,500, in Fig. 2 of 784B2, simplify and illustrate like that, angiography roentgen radiation system also has the fixing device for the common ceiling of C shape arm 2 or floor installation.
Known a kind of for automatically determining the method for rebuilding optimum cardiac phase for heart CT from DE 10 2,007 029 731 A1, wherein carry out:
-with spiral CT, along z axis, patient's heart area is sampled, and with first resolution, be reconstituted in the image data set of the different locational a plurality of fault imagings of z,
-measure cardiomotility, determine cycle and the periodic phase of heart, and associated with image data set that rebuild, first resolution,
-generation Dynamic Graph,
-shade (Maskierung) is about the Dynamic Graph of each cardiac cycle,
-determine in Dynamic Graph that each is by two motion minima of mask regions, and by the end phase association of the contraction of these minima and heart or diastole,
-with second resolution, by the measurement data relevant with the determined cardiac phase of at least one determined minima, rebuild at least one image data set, and
-with second resolution, show this at least one image data set of rebuilding.
At Carsten Oliver Schirra etc., be published in Computerized Medical Imaging and Graphics, the 33rd volume, in the 122nd 130 pages of – " Improvement of CardiaC CT-Reconstruction using local motion vector fields ", in order to reduce motion blur and improvement signal to noise ratio (S/N), described a kind of reconstruction of motion correction, proposed the local field of the motion vector of high contrast object for the motion correction in filtered back projection.Carries out image registration during the cardiac phase of tranquillization.Temporal interpolation in parameter space is for determining the motion during the cardiac phase with strong movements.The field of formed motion vector is used to image reconstruction.
Summary of the invention
The technical problem to be solved in the present invention is, sets up a kind of angiography method that type is mentioned in beginning, makes to reduce at the relevant 4D rotational angiography of heart, so-called
middle stricture of vagina shape artifact.
This technical problem solves for angiography method as follows according to the present invention:
S1) acquired projections image on different cardiac phases and position,
S2) from projected image, rebuild the 3D volumetric image in different cardiac phases,
S3) from 3D volumetric image, calculate Dynamic Graph,
S4) 3D volumetric image and Dynamic Graph are carried out to image combining, to produce consequent, the corrected 3D volumetric image in different cardiac phases, and
S5) consequent, corrected 3D volumetric image is shown.
This method according to this invention is utilized redundant data, for example, to (reduce 4D rotational angiography that heart is relevant
image in stricture of vagina shape artifact.
Accompanying drawing explanation
Next by embodiment illustrated in the accompanying drawings, elaborate the present invention.Wherein:
Fig. 1 shows with respectively as known, the biplane C shape arm angioradiographic system of the industrial robot of supporting arrangement,
Fig. 2 shows with the situation in the relevant collection of EKG during rotating according to the rotational angiography system of Fig. 1,
Fig. 3 comes according to the series of the projected image of Fig. 2 collection according to the standard technique method of angiography,
The Dynamic Graph that Fig. 4 sets up from the 3D volumetric image of rebuilding,
Fig. 5 to 8 shows for processing the figure of the Dynamic Graph of setting up according to Fig. 4 again and sets forth,
Fig. 9 illustrates the linear image combination of carrying out with linear interpolation, and
Figure 10 to 13 has set forth time flow and its result of processing again with graphics mode.
The specific embodiment
Figure 2 illustrates during rotation the situation of the collection that EKG to carry out according to the C shape arm equipment of Fig. 1 is relevant, at 90bpm, the persistent period to the heart rate of 131bpm, 10s to 15s and band are with or without cardiac phase and control (Pacing(pace-making) for it) carry out.If do not carry out pace-making, cause the known manual sort to the phase place from EKG.
A shown in this figure EKG13, it has different cardiac phase c
0to c
n.These cardiac phases c
0to c
nassociated from different projected angle θ 0 to θ 0+n* Δ θ.So the first image 14 value of drawing p (θ for the first cardiac phase c0
0, c
0), for the first image 15 value of drawing p (θ of the second cardiac phase
0+ Δ θ, c
1), for the first image 16 value of drawing p (θ of the 3rd cardiac phase
0+ 2 Δ θ, c
2), for the first image 17 value of drawing p (θ of N cardiac phase
0+ N Δ θ, c
n).
This can continue as represented by arrow 18 symbols, until arrive the 2nd EKG19.
These cardiac phases c
0to c
nassociated to θ 0+ (n+N) * Δ θ from different projected angle θ 0+n* Δ θ again.So for the first cardiac phase c
0the second image 20 value of drawing p (θ
0+ n Δ θ, c
0), for the second image 21 value of drawing p (θ of the second cardiac phase
0+ (n+1) Δ θ, c
1), for the second image 22 value of drawing p (θ of the 3rd cardiac phase
0+ (n+2) Δ θ, c
2), for the second image 23 value of drawing p (θ of N cardiac phase
0+ (n+N) Δ θ, c
n).
Figure 3 illustrates according to standard method in the situation that the sweep time of 120bpm and 13s, the series of the projected image 24 of setting up with about 30 projections of each cardiac phase, it has interfering stricture of vagina shape artifact 25.Labelling c
0to c
nthe projected image 24 that represents current cardiac phase.
Fig. 4 shows the sequence of the 3D volumetric image 26 of reconstruction, and it is set up with about 30 projections of each cardiac phase, from these 3D volumetric images according to formula
Calculate 27 sports cards or motion sketches based on image, be so-called motion diagram or dynamic Figure 28.The labelling f of 3D volumetric image 26
c0to f
cNbe illustrated in corresponding cardiac phase (c
0to c
n) in the 3D volume rebuild and comprise image information.
Because dynamic Figure 28 is the noisy stricture of vagina shape of tool artifact 25 also, so carry out processing again of dynamic Figure 28, it elaborates by Fig. 5 to 8.
A kind of method is to analyze frequency domain.In Fig. 5, observe in 3D volumetric image 26 and two pixels 29 dynamically selecting typically in Figure 28 and 30, wherein the first pixel 29 has low-frequency large motion, and the second pixel 30 has high-frequency little motion.
Fig. 6 reflects the signal intensity curve of pixel 29 and 30, and wherein the signal intensity curve 31 of the first pixel 29 has the low frequency of signal intensity curve 32 than the second pixel 30.
In Fig. 7, about spatial frequency u, drawn now the modulation case of heart movement and stricture of vagina shape artifact 25, wherein show the signal intensity curve 33 of modulation of the first pixel 29 and the signal intensity curve 34 of the modulation of the second pixel 30, it has modulation direction 35.
Fig. 8 shows about spatial frequency u and has drawn the situation after demodulation heart movement and stricture of vagina shape artifact 25, the signal intensity curve 37 after the demodulation of its signal intensity curve 36 after with the demodulation of the first pixel 29 and the second pixel 30.
The principle of modulation and demodulation mainly, for example, on some positions, the pixel value in the second pixel 30 only changes to paracycle due to stricture of vagina shape artifact 25.These quasi-periodic variations of stricture of vagina shape artifact 25 are based on so-called windmill effect (Windm ü hlen-Effekt).They are the sampling artifacts (Abtastartefakt) as time function.On other position, for example, in the first pixel 29, can be based on windmill effect and cardiac motion artefacts and the variation as time function of inferring this pixel 30.Such variation can be identified, and it can be for example, by wave filter (demodulation) by optionally soft Jiao (Weichzeichnug) processing.
The principle of modulation and demodulation is conventionally known from signal theory or signal processing, at this, can use Fourier analysis or bandpass filtering.Modulate givenly by shooting itself, demodulation is for separated with " truly " signal by " carrier wave " signal.In the specific shooting form here relating to, it is relatively simple, because windmill artifact has very the frequency limiting, it is only with to take geometry relevant, and therefore calculated in advance simply.
Dynamically the morphological operation (for example corrode and/or expand) of Figure 28 can be as other for processing the method for dynamic Figure 28 again.
Also can be for example, by the sub sampling of dynamic Figure 28 and interpolation method (bilinearity or Spline Interpolation Method) for processing again.
The result of processing again by one of these methods as dynamic Figure 28 obtains corrected Dynamic Graph, and it does not almost have stricture of vagina shape artifact 25.
The example of image combining shown in Figure 9 is the linear combination of being undertaken by linear interpolation.Yet can also be other composite type, the image combining of polynomial or secondary for example.It is also conceivable that the image combining being undertaken by convolution operator.
By Fig. 9, illustrate now one of possible image combining, it draws conventionally from equation below:
C wherein
nrepresent corresponding cardiac phase c
0to c
n.
Pixel f (x, y, z, the c of the 3D volumetric image 26 of rebuilding
n) multiply each other with the pixel MM (x, y, z) of corrected dynamic Figure 38.By the Dynamic Graph 38MM (x, y, z) by with 1 correction down with about the average image 39 of all phase images
the product and its addition that form.F (x, y, z, c as a result of
n) obtain formed, corrected 3D volumetric image 40.
This multiplies each other is the simple scenario of image combining, wherein in each phase place, always carry out two images (or volume) according to pixels or multiply each other (weighting) of voxel, wherein Dynamic Graph is remaining unchanged after processing again.
In other words, the first cardiac phase c
0the result of example as follows:
This exemplarily so illustrates for linear interpolation.The in the situation that of nonlinear combination, must limit corresponding function f (MM (x, y, z)), for example in multinomial mode, limit.Mainly be in this case each volume weighting corresponding to Dynamic Graph.
The result of processing again also can elaborate and symbolically illustrate by Figure 10 to 13, and it has reflected the time sequencing that image forms.Starting point is the image sequence " before Dynamic Graph-process again " of the 3D volumetric image 26 rebuild.Calculate thus dynamic Figure 28.Then by the processing of describing, this dynamic Figure 28 is proofreaied and correct to " Dynamic Graph-process again " for corrected dynamic Figure 38 in Fig. 5 to 8.Finally, according to above mentioned equation, calculate consequent, corrected 3D volume Figure 40 " after Dynamic Graph-process again ".
Method presented above based on rebuild layer, be that 3D volumetric image 26 is worked.
Grab type is to sample to rotate with good angle, for example the sampling time of 13s, the angle step of 0.5 ° and 2 * 2 vanning.Form thus about 380 projections about all phase places.Utilize information that exist, redundancy, because the only several voxels in image change.The variation of voxel is calculated by dynamic Figure 28 of every layer.Dynamically Figure 28 reflects the variation about the time of motion composition or voxel value.Voxel have in heart be arranged in other body part from it time different movement function, change function or gradient.
Dynamically Figure 28 is also subject to the impact of stricture of vagina shape artifact 25 in first step.In order to reduce these artifacts, three kinds of Retreatment methods have been proposed, so that the variation that the variation causing by stricture of vagina shape artifact 25 is caused with heart movement by pure is separated.Cause thus the minimizing of stricture of vagina shape artifact 25 in dynamic Figure 28.
Dynamically Figure 28 is for example used as, at the reconstruction of single phase place (c0) and the combining weights between the meansigma methods image of all phase places.In this hypothesis, the voxel value that dynamically in Figure 28, numerical value is little is less to the contribution of heart movement.
Image combining can complete by linear interpolation, yet other composite type is also possible.
Consequent, corrected 3D volumetric image 40 has significantly less stricture of vagina shape artifact 25.
The method according to this invention can be for monoplane and bi-plane systems.Contrary with many other known methods, it is the pure method based on image.Neither need initial data, also do not need how much or out of Memory.
By the method according to this invention, with limited room and time resolution loss by stricture of vagina shape artifact 25 from 4D rotational angiography, so-called
in image, be close to fully and eliminate.
The generation of dynamic Figure 28 and again processing further reduce interfering stricture of vagina shape artifact 25.
The method according to this invention also can for example, for other agreement of the variation with in time orientation (Zeitrichtung), perfusion.
For calculating, effectively utilized the reconstruction chain existing.
Claims (5)
1. by 4D rotational angiography, patient's conduct is checked to the angiography method that organ, vascular system or other body region of object carry out, it is characterized in that following steps:
S1) gather different cardiac phase (c
0to c
n) and position in projected image (24),
S2) from described projected image (24), rebuild different cardiac phase (c
0to c
n) in 3D volumetric image (26),
S3) from described 3D volumetric image (26), calculate Dynamic Graph (28,38),
S4) described 3D volumetric image (26) and described Dynamic Graph (28,38) are carried out to image combining, to produce different cardiac phase (c
0to c
n) in consequent, corrected 3D volumetric image (40), and
S5) described consequent, corrected 3D volumetric image (40) is shown.
2. angiography method according to claim 1, is characterized in that, forms the meansigma methods image (39) about all cardiac phases from described 3D volumetric image (26)
according to method step S4) image combining in consider this meansigma methods image.
3. angiography method according to claim 1 and 2, is characterized in that, according to following equation, calculates described consequent, corrected 3D volumetric image (40):
Wherein,
-c
neach cardiac phase c
0to c
n,
-f (x, y, z, c
n) be the 3D volumetric image (26) of rebuilding,
-MM (x, y, z) is Dynamic Graph (28,38),
-
the meansigma methods image (39) about all phase images, and
-F (x, y, z, c
n) be consequent, corrected 3D volumetric image (40).
4. angiography method according to claim 3, is characterized in that, described Dynamic Graph (28,38) is Dynamic Graph that processed again, corrected (38).
5. according to the angiography method one of claim 1 to 4 Suo Shu, it is characterized in that, according to method step S3) calculate as follows described Dynamic Graph (28):
The labelling f of wherein said 3D volumetric image (26)
c0to f
cNrepresent corresponding cardiac phase (c
0to c
n) in the 3D volume of reconstruction.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| DE102012216652.1A DE102012216652B4 (en) | 2012-09-18 | 2012-09-18 | Angiographic examination procedure |
| DE102012216652.1 | 2012-09-18 |
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| Publication Number | Publication Date |
|---|---|
| CN103654823A true CN103654823A (en) | 2014-03-26 |
| CN103654823B CN103654823B (en) | 2016-04-20 |
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| CN201310371018.8A Active CN103654823B (en) | 2012-09-18 | 2013-08-23 | Angiographic examination method |
Country Status (3)
| Country | Link |
|---|---|
| US (1) | US20140081131A1 (en) |
| CN (1) | CN103654823B (en) |
| DE (1) | DE102012216652B4 (en) |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106999129A (en) * | 2014-11-25 | 2017-08-01 | 皇家飞利浦有限公司 | Digital subtraction angiography |
| CN107913078A (en) * | 2016-10-11 | 2018-04-17 | 西门子保健有限责任公司 | Method for determining data perfusion group |
| CN109767468A (en) * | 2019-01-16 | 2019-05-17 | 上海长征医院 | Internal organs volume detection method and device |
| CN113395935A (en) * | 2019-02-06 | 2021-09-14 | 威廉·E·巴特勒 | Spatio-temporal reconstruction of moving vessel pulse waves from multiple lower-dimension angiographic projections |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US9427200B2 (en) | 2014-03-21 | 2016-08-30 | Siemens Aktiengesellschaft | Determination of physiological cardiac parameters as a function of the heart rate |
| JP6707542B2 (en) | 2014-12-18 | 2020-06-10 | コーニンクレッカ フィリップス エヌ ヴェＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｎ．Ｖ． | Imaging system for imaging an elongated region of interest in an object |
Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20040136490A1 (en) * | 2002-07-23 | 2004-07-15 | Edic Peter Michael | Method and apparatus for correcting motion in image reconstruction |
| US20060133564A1 (en) * | 2004-12-21 | 2006-06-22 | David Langan | Method and apparatus for correcting motion in image reconstruction |
| DE102007029731A1 (en) * | 2007-06-27 | 2009-01-02 | Siemens Ag | Automatic determination of an optimum heart phase for computer tomography reconstruction, masks a motion map from image data sets to determine movement minima for the systolic and diastolic end phases |
| US20090252378A1 (en) * | 2008-04-02 | 2009-10-08 | Siemens Aktiengesellschaft | Operating method for an imaging system for the time-resolved mapping of an iteratively moving examination object |
Family Cites Families (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5696848A (en) * | 1995-03-09 | 1997-12-09 | Eastman Kodak Company | System for creating a high resolution image from a sequence of lower resolution motion images |
| US6539074B1 (en) * | 2000-08-25 | 2003-03-25 | General Electric Company | Reconstruction of multislice tomographic images from four-dimensional data |
| DK1494579T3 (en) * | 2002-04-02 | 2011-11-14 | Yeda Res & Dev | Characterization of moving objects in a stationary background |
| CN100583155C (en) * | 2004-06-18 | 2010-01-20 | 皇家飞利浦电子股份有限公司 | Artifact reduction |
| DE102005012700B4 (en) | 2005-03-18 | 2012-08-23 | Siemens Ag | X-ray device |
| EP1869643B1 (en) * | 2005-04-07 | 2014-05-07 | Koninklijke Philips N.V. | Image processing device and method for blood flow imaging |
| JP2012515592A (en) * | 2009-01-21 | 2012-07-12 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | Method and apparatus for large field imaging and motion artifact detection and compensation |
| BR112012014173A2 (en) * | 2009-12-15 | 2016-05-17 | Koninkl Philips Electronics Nv | method and data compensator |
| US20110148928A1 (en) * | 2009-12-17 | 2011-06-23 | General Electric Company | System and method to correct motion in gated-pet images using non-rigid registration |
| US8761467B2 (en) * | 2010-10-04 | 2014-06-24 | General Electric Company | Method and apparatus for assessing motion correction |
| US8600132B2 (en) * | 2011-05-03 | 2013-12-03 | General Electric Company | Method and apparatus for motion correcting medical images |
| US8897527B2 (en) * | 2011-06-07 | 2014-11-25 | Varian Medical Systems, Inc. | Motion-blurred imaging enhancement method and system |
-
2012
- 2012-09-18 DE DE102012216652.1A patent/DE102012216652B4/en active Active
-
2013
- 2013-08-23 CN CN201310371018.8A patent/CN103654823B/en active Active
- 2013-08-28 US US14/012,014 patent/US20140081131A1/en not_active Abandoned
Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20040136490A1 (en) * | 2002-07-23 | 2004-07-15 | Edic Peter Michael | Method and apparatus for correcting motion in image reconstruction |
| US20060133564A1 (en) * | 2004-12-21 | 2006-06-22 | David Langan | Method and apparatus for correcting motion in image reconstruction |
| DE102007029731A1 (en) * | 2007-06-27 | 2009-01-02 | Siemens Ag | Automatic determination of an optimum heart phase for computer tomography reconstruction, masks a motion map from image data sets to determine movement minima for the systolic and diastolic end phases |
| US20090252378A1 (en) * | 2008-04-02 | 2009-10-08 | Siemens Aktiengesellschaft | Operating method for an imaging system for the time-resolved mapping of an iteratively moving examination object |
Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106999129A (en) * | 2014-11-25 | 2017-08-01 | 皇家飞利浦有限公司 | Digital subtraction angiography |
| CN106999129B (en) * | 2014-11-25 | 2020-11-03 | 皇家飞利浦有限公司 | Digital subtraction angiography |
| CN107913078A (en) * | 2016-10-11 | 2018-04-17 | 西门子保健有限责任公司 | Method for determining data perfusion group |
| CN109767468A (en) * | 2019-01-16 | 2019-05-17 | 上海长征医院 | Internal organs volume detection method and device |
| CN113395935A (en) * | 2019-02-06 | 2021-09-14 | 威廉·E·巴特勒 | Spatio-temporal reconstruction of moving vessel pulse waves from multiple lower-dimension angiographic projections |
| CN113395935B (en) * | 2019-02-06 | 2023-11-24 | 威廉·E·巴特勒 | Method and computer system for reconstructing a representation of heart beat frequency angiography |
Also Published As
| Publication number | Publication date |
|---|---|
| DE102012216652B4 (en) | 2023-01-26 |
| DE102012216652A1 (en) | 2014-03-20 |
| CN103654823B (en) | 2016-04-20 |
| US20140081131A1 (en) | 2014-03-20 |
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